WO2022122246A1

WO2022122246A1 - Retention device and method for separating cells

Info

Publication number: WO2022122246A1
Application number: PCT/EP2021/079852
Authority: WO
Inventors: Tanja Maucher; Jochen Hoffmann; Astrid LUX; Hannah Bott
Original assignee: Robert Bosch Gmbh
Priority date: 2020-12-09
Filing date: 2021-10-27
Publication date: 2022-06-16
Also published as: DE102020215567A1

Abstract

Described is a retention device (4) for separating cells that are in a cell suspension, said retention device (4) comprising at least one feeding unit (1) and a retention element (2), in particular a microfilter and/or a microstrainer with pores, the retention device (4) further comprising an optical detection unit (5) for the real-time optical detection of cells retained by the retention element (2) and/or cells where penetration of the retention element (2) is delayed.

Description

description

title

Retention device and method for separating cells

The present invention relates to a retaining device and a method for separating cells located in a cell suspension and to a cartridge comprising the retaining device according to the preamble of the independent claims.

State of the art

WO 2012/159820 A1 describes an automated detection of circulating tumor cells from body fluids, which are held back by means of a porous membrane. A process liquid is then applied to the membrane, which marks the cells to be detected so that they can be examined optically after filtering and staining.

WO 00/06702 A1 describes a method and a kit for isolating cancer cells from a body fluid using a sieve or membrane filter. The liquid is passed through the sieve, which retains the cancer cells because of their size. The isolated cells can then be examined following filtration.

DD 222 827 A5 describes the selection of specific biological cells. For this purpose, a filter with a large number of recesses is used, the recesses penetrating the filter from top to bottom and having a predetermined shape and dimension. For example, the diameter steadily decreases from the top to the bottom, so that the recesses run conically and the specific cells are held in the recesses and are thus selected according to their size on the one hand and separated on the other. Subsequently, the cells remaining in the filter can be analyzed using an optical system.

DE 10 2011 076 238 A1 describes a support body for a porous filter membrane. A liquid sample is filtered by means of the filter membrane and circulating tumor cells in particular are retained. The transparent supporting body is formed in a carrier which essentially corresponds to a slide for a microscope. The filter membrane rests on the transparent support body and is connected to it. The filtrate can run off through holes or pores in the support body. The circulating tumor cells are then analyzed using light microscopy or fluorescence microscopy.

The separation and identification of different cells from suitable liquids is an important step in the research, diagnosis and treatment of diseases. After isolating the specific cells, clinically relevant characteristics and information can be obtained from the cells.

Circulating tumor cells (CTCs), for example, have established themselves as promising and clinically relevant biomarkers for diagnosing malignant tumors in recent years. Their earliest possible detection in suitable liquids such as blood or lymphatic fluid, also known as liquid biopsy, is one of the research priorities of modern oncology. For example, a time-resolved quantification of CTCs of a cancer patient allows the course of the disease to be tracked precisely and in real time and therapy decisions to be made that are tailored to the individual disease situation.

For this it is of great importance to be able to detect as many of the cells to be detected as possible. Disclosure of Invention

According to the invention, a retention device and a method for separating cells in a cell suspension, as well as a cartridge containing the retention device, are provided with the characterizing features of the independent claims.

This is based in particular on the fact that the retaining device for separating cells in a cell suspension comprises a feed unit and a retaining element, in particular a microfilter and/or a microsieve with pores, and an optical detection unit for optical real-time detection of cells retained by the retaining element and/or cells whose passage through the retaining element is delayed.

The retention rate of cells to be separated from a cell suspension is determined by parameters such as the pore size and pore shape of the retention element, the porosity, rigidity and thickness of the retention element, as well as the volume flow and filtration pressure, as well as any pressure differences to which the retention element and the cell suspension are exposed, the cell diameter of the cells to be separated, as well as surface interactions between the cells of the cell suspension and the retaining element.

For cells in a certain size range, the passage through a retaining element is a time-dependent process because, in addition to the parameters mentioned, which also influence the passage time, smaller and deformable cells also pass through the pores of the retaining element much more quickly than larger and stiffer cells. For example, cells in a certain size range, which are initially retained by the retaining element, can pass this after a certain time, for example because of their deformability.

By the term deformable it is meant that the cell is elastic and can deform to some extent. The term deformation is also used for this property in the present description of the invention. With conventional filtration approaches, the number of cells retained by the retention element is only determined after the filtration process. Cells that are initially held back by the retaining element but then pass through after a short time, for example as a result of cell deformation, are not recorded here.

The advantage of the restraining device according to the invention is that the cells to be detected are detected in real time during the restraining process, and thus cells whose passage through the restraining element is delayed are also detected. In this way, a larger number of cells to be detected can be recorded, which leads to a more precise result.

In order to be able to determine the retention rate of the cells to be detected, i.e. the target cells, with conventional retention methods it is necessary either to determine the initial concentration of the cells to be detected in the cell suspension or to determine the number of cells to be detected which are not retained by the retention element were determined from the filtrate. This requires further microfluidic and optical devices and process steps. The advantage of the restraining device according to the invention is that, for example, the number of cells to be detected is recorded quantitatively in real time during the restraining process. With real-time detection, the initial concentration of the target cells is determined directly with negligible losses. No further optical devices or process steps are necessary to be able to determine the retention rate, which saves time, tools and work steps.

In addition, it is advantageous if the restraint device has a feed unit with two or more feed channels. When the cell suspension flows through the retaining element, a homogeneous distribution of the cell suspension on the retaining element is achieved, so that the retained cells are not concentrated on part of the surface of the retaining element, but rather are distributed over the surface of the retaining element. As a result, the pressure difference before and after the retaining element is kept as small as possible, so that many cells to be detected are retained on the retaining element for as long as possible. This improves the optical detection of the cells to be detected in real time while the cell suspension flows through the retaining element. In an advantageous embodiment, the two or more feed channels of the feed unit connect to form one large feed channel via the retaining element.

Further advantageous embodiments emerge from the dependent claims.

It is advantageous if the retaining element is made at least partially from an optically transparent material, in particular from a polycarbonate and/or a cycloolefin copolymer (COC) and/or from a glass.

The advantage of using a polycarbonate is that it has high impact strength and is light in weight.

The advantage of using a glass is that it is largely scratch-resistant and therefore very durable.

The advantage of using a COC is that it can be produced inexpensively, is break-resistant and has a low density and low weight.

In a further advantageous embodiment, the pores of the retaining element have a diameter of 3 μm-20 μm, preferably 4 μm-8 μm.

Such pore diameters are advantageous, for example, when separating CTCs from a cell suspension. Most CTCs have a slightly larger diameter and are less deformable than, for example, leukocytes, so that the CTCs are selectively prevented from passing through the retaining element.

In a further advantageous embodiment, the retaining element has an area of 1 mm ² -500 mm ² , preferably 3 mm ² -100 mm ² , which can be exposed to a cell suspension. It is advantageous here that the cells of a sample volume of a cell suspension of, for example, 20-300 μl are distributed statistically on the retaining element with such an area that the distance between the cells allows good optical detection.

Furthermore, it is advantageous if the retaining element has a thickness of 0.9 μm-20 μm, preferably 1 μm-12 μm. The advantage of such a thickness is that deformable cells take a long enough time, for example one or more minutes, to be able to pass through the retaining element. The delayed passage of the cells through the retaining element ensures that the cells are detected optically.

The subject matter of the invention is also a method for separating cells, in particular living cells, located in a cell suspension by means of a retaining device according to the invention with the following steps: b) supplying the cell suspension to the device with retaining element c) optical detection of the cells retained by the retaining element and/or or of the cells whose passage through the retaining element is delayed, the detection taking place in real time during the passage of the cell suspension through the retaining element.

The resulting advantages have already been described above for the restraint device according to the invention.

In addition, it is advantageous that the viability of the cells to be detected is not impaired, so that on the one hand the cells exhibit their typical behavior and phenotypic characteristics upon detection and on the other hand further analyzes can be carried out with the cells following the detection.

In an advantageous embodiment of the method, step b) is preceded by an additional step a): a) labeling of the cells to be detected in the cell suspension, with the viability of the cells to be detected in particular being retained.

In step c), the marked cells retained by the retaining element and/or the marked cells whose passage through the retaining element is delayed is then optically detected, the detection taking place in real time while the cell suspension is flowing through the retaining element. In conventional methods, filtration often takes place first, followed by staining steps, for example on the retention element itself, and subsequent detection of the cells to be detected. Before staining, for example on the retaining element, the cells to be detected are often treated with a fixing solution, such as formaldehyde, which makes it possible to stain structures inside the cells. However, this inactivates and preserves the cells.

The advantage of the staining strategy on which this invention is based, with a marking preceding the separation process, is that the cells to be detected can already be detected while they are flowing through the retaining element.

In addition, there is no need to fix the cells, for example on the retaining element, so that the viability of the marked cells to be detected is retained. In this way, when they are detected, typical behaviors and phenotypic characteristics of the marked cells to be detected can be observed and recorded in real time. In addition, further analyzes can be carried out with the living cells after detection or, for example, molecular diagnostic analyses. For this purpose, the retained cells are lysed, for example with a total cell lysis buffer, for example transferred to an external sample vessel and the deoxyribonucleic acids (deoxyribonucleic acid, DNA) and ribonucleic acids (ribonucleic acid, RNA) of the cells are extracted. Further analyzes can also be carried out with the cells which pass through the retention element, ie which are present in the filtrate.

It is advantageous here if the cells to be detected are labeled by staining with carboxyfluorescein succinimidyl ester (CFSE) and/or with propidium iodide (PI) and/or by labeling of surface antigens, in particular by fluorescent antibodies and/or by means of a label that binds deoxyribonucleic acid .

CFSE is a fluorescent cell-staining dye that is cell-permeable and covalently couples to certain intracellular molecules via its succinimidyl group.

The advantage here is that CFSE is only enzymatically converted to the fluorescent dye in living cells, so that only living cells are deleting cells are determined. Another advantage is that the cells to be detected do not have to be fixed for staining.

Furthermore, the cells can be labeled with PI, which is a fluorescent dye that intercalates specifically in nucleic acids. Since PI can only penetrate the perforated cell membrane of dead cells, but not the intact cell membrane of living cells, dead cells to be detected can be detected in this way. A combined staining with CFSE and PI allows a combined visual differentiation between living and dead cells to be detected. This is of great importance, for example, when it comes to researching, diagnosing or treating diseases. In cancer patients, for example, only living tumor cells pose a risk of metastasis. The number of living cells is therefore decisive here.

It is also advantageous that the cells to be detected do not have to be fixed for labeling with PI.

Furthermore, various surface antigens of the cells to be detected can be detected.

Antigens are mostly proteins, but can also be carbohydrates, lipids or other substances to which specific antibodies can bind, for example. Examples of such antigens are the epithelial cell adhesion molecule (EpCAM) and cytokeratins.

EpCAM is a surface protein and cell adhesion molecule found on various epithelial cells, which is responsible for cell-cell contacts, for example. For example, EpCAM is considered to be one of the typical markers for CTCs.

Cytokeratins are proteins found inside cells of epithelial origin. Different epithelial cells express different cytokeratins on their cell surface. Cytokeratins are typical markers in diagnostic pathology, especially for the detection of tumors. For example, different tumors can be distinguished from other tumors based on the same pattern of cytokeratins. Certain cytokeratins are thus markers for CTCs, for example.

Allophycocyanin (APC) is a pigment involved in the photosynthesis of cyanobacteria and red algae, as well as a bright fluorescent dye. Allophycocyanin can be coupled to an antibody so that specific antigens of target cells can be detected by fluorescence microscopy after binding.

A fluorescently labeled antibody that binds to EpCAM is, for example, anti-EpCAM allophycocyanin. A cytokeratin-binding fluorescently labeled antibody is, for example, anti-cytokeratin allophycocyanin. The advantage of using the two antibodies mentioned is that they can be used to specifically detect cells that are to be detected. In addition, these are non-toxic for the cells to be detected and maintain their viability. In addition, the cells to be detected do not have to be fixed for labeling.

Furthermore, cells with a nucleus can be distinguished from cells without a nucleus by means of certain markings or staining of the DNA within the cell nuclei. Nucleated cells can be detected, for example, using the fluorescent dye 4',6-diamidine-2-phenylindole (DAPI), which labels the DNA. DAPI penetrates intact cell membranes, but only slowly. The advantage here is that the viability of the cells to be detected is retained and it is not necessary to fix the cells to be detected for labeling.

Furthermore, the fluorescent dye 2'-(4-ethoxyphenyl)-5-(4-methyl-l-piperazinyl)-2,5'-bi-lH-benzimidazole trihydrochloride (Hoechst 33342) can be used to stain DNA. Hoechst 33342 has proven itself in experiments with living cells and offers the advantages that the viability of the cells to be detected is retained and they are also stained very quickly. It is also advantageous that the cells to be detected do not have to be fixed for marking.

It is also advantageous if at least one of the following parameters is detected in step c): number of cells to be detected and/or diameter of the cells to be detected and/or cell contour of the cells to be detected and/or transit time of the cells to be detected through the Retaining element and/or determining the deformation of the cells to be detected when passing through the retaining element and/or the homogeneity of the labeling agent embedded or bound in the cells to be detected. The advantage here is that compared to conventional approaches to the separation of cells, in which the cells to be detected are only detected after the retention process, a lot of additional information about the cells, which can only be determined in this form in real time during the passage process, is collected. Such information is, for example, the passage time and the deformation capacity of a cell, which is initially retained by the retaining element and then after a certain time passes through it.

Furthermore, it is advantageous that extensive information about the cells to be detected can be collected in this way, on the basis of which more precise statements can be made, for example, about a clinical picture, the course of a disease or other treatment options. In addition, relationships between the cells to be detected, their characteristics and a typical clinical picture can be determined in this way, such as statements about the heterogeneity of a tumor in cancer patients.

In an advantageous embodiment, the cells to be detected are detected by recording individual images at defined time intervals, in particular after 0.1-60 seconds, preferably after 1-10 seconds. The frame rate is an individually adjustable parameter.

When recording individual images, it is advantageous that in particular the entire surface of the retaining element is recorded optically and in this way many more cells to be detected can be identified in comparison to conventional methods. Such conventional methods are, for example, measurement using a flow cytometer, where cells are optically recorded as they flow past a measuring point, or filtration approaches, in which those cells to be detected that pass through the pores of the retention element immediately or after a short retention time due to cell deformation are often lost .

Another advantage of detection by recording individual images is that very precise results are determined. In addition, a single cell characterization is possible, with individual cells being observed, so that conclusions can be drawn about the passage time through the retaining element and the deformability of the cells to be detected. Furthermore, the cell suspension is a blood sample, for example. For example, clinically relevant information can be obtained from the cells that are in the blood, which allow an up-to-date picture of the health or illness of the blood donor.

For example, the blood sample is pretreated, for example by selective lysis of the erythrocytes.

The cells to be detected are, for example, circulating tumor cells. CTCs are cells of epithelial origin that have detached from a primary tumor cell cluster and entered the lymphatic vessels or the bloodstream and circulate there. Some CTCs are able to migrate to distant organs and form metastases there.

CTCs have a cell nucleus and often carry the proteins EpCAM and cytokeratins on their cell surface. CTCs are often larger and less deformable than other blood cells. Thus, CTCs can be separated from other, smaller blood cells by means of a retaining element with a suitable pore diameter. However, the size of the CTCs is highly dependent on their site of origin and the type of tumor. Rarely, there are also CTCs that are smaller than blood cells. With conventional filtration approaches, the number of cells retained by the retention element is determined after the filtration process. CTCs that are initially held back by the restraining element but then pass through after a short time are not recorded here. The advantage of the method according to the invention is that the CTCs are detected in real time during the restraining process, and thus those CTCs whose passage through the restraining element is delayed are also detected. In this way, a larger number of CTCs can be recorded. This leads to a more precise result, which in turn provides valuable information for the classification and treatment of a tumor.

In an advantageous embodiment, a pump pumps the cell suspension through the retention device at a constant flow rate, the flow rate being in particular between 0.01 pl/s and 100 pl/s, preferably between 0.2 pl/s and 5 pl/s.

The advantage here is that the acting shear forces do not change the cells of the cell suspension, for example in the microfluidic environment, in this flow rate range to such an extent that they can no longer be retained by the retaining element or optically detected. The advantage here is that, taking into account the shear forces acting at such flow rates, it is ensured that the cells of the cell suspension to be detected, for example in a microfluidic environment, are retained by the retaining element and can be detected optically and are not changed in such a way that they cannot more can be retained or optically detected by the retaining element. Furthermore, the total time in which the cell suspension is pumped through the retention device is reduced as much as possible, while the cells to be detected continue to be captured by the optical system.

Different constant flow rates can also be set for several passes to separate cells using the retention device according to the invention, so that different dynamics and behavior of the cells to be detected can be observed when passing through the retention element, such as differences in the dwell time on the retention element before passage or Differences in the deformability of the cells to be detected.

In an alternative advantageous embodiment, a pump pumps the cell suspension through the retention device at a varying flow rate, the flow rate being in particular between 0.01 pl/s and 100 pl/s, preferably between 0.2 pl/s and 5 pl/s.

A varying flow rate means that the pressure difference before and after the retaining element also varies.

The advantage here is that the cells that are already retained by the retaining element are not continuously pressurized and can therefore remain longer on the retaining element, so that they can be detected longer and, if necessary, can be detached from the retaining element again by increasing the flow rate becomes.

In many common chip laboratory systems (Lab on a chip, LoC), which represent microfluidic systems for the automated analysis of samples on a chip, only pulsatile flow rate profiles are often possible. The advantage of the described embodiment of the invention with a pulsatile flow profile is that this method can be integrated into such a LoC system.

In the described embodiment with a pusatile flow profile, the pump is, for example, a peristaltic pump. In general, a conveying element other than a pump may be used to practice the present invention.

In a further advantageous embodiment, the cell suspension is fed to the retaining element in portions as aliquots and the cells retained by the retaining element are removed from the retaining element after each aliquot or after a predetermined number of aliquots. The advantage of feeding in portions as aliquots is that the pressure difference that occurs as soon as a large part of the surface of the retaining element is covered with cells is kept as small as possible. In this way, as many cells as possible to be detected are retained on the retaining element for as long as possible, as a result of which more cells to be detected can be detected. Another advantage is that the cells to be detected can be separated and recorded from a significantly larger volume of cell suspension. In addition, the cells to be detected can be identified and recorded against a higher background of cells not to be detected.

Furthermore, it is advantageous if the cells retained by the retaining element are removed from the retaining element after each aliquot or after a predetermined number of aliquots, since in this way more precise results are obtained for analyzes of the next aliquot or aliquots. The cells retained by the retention element can be removed, for example, by increasing the pressure difference across the retention element or by lysing the cells retained by the retention element.

The subject matter of the invention is also a cartridge, in particular a microfluidic cartridge, as described for example in DE102016222072A1 or DE102016222075A1, comprising the retaining device described above. The method steps described for the separation of cells located in a cell suspension then all take place, for example, inside the cartridge. A pretreatment of the cell suspension can also take place within the cartridge, as well as process steps for labeling the cells to be detected. In addition, the retained by the retaining element cells after detection within the Cartridge are lysed and the cell lysate are then transported, for example, in an additional sample chamber on the cartridge. In this, for example, the DNA and/or RNA of the lysed cells can be extracted for further analysis without the need for an additional external system.

Brief description of the drawing

Embodiments of the present invention are shown in the drawing and explained in more detail in the following description of the figures. It shows:

1a: the schematic representation of a cross section through a restraint device according to the invention in a first embodiment with restraint element and a feed unit with a feed channel,

Fig. Lb: the schematic representation of a top view of the invention

restraint device according to Fig. 1,

2: the schematic representation of a plan view of a restraint device according to the invention in a second embodiment with restraint element and a feed unit with two feed channels,

3a: the schematic representation of a top view of a retaining element according to FIG

1 or 2 after a first period of time,

3b: the schematic representation of a top view of a retaining element according to FIG

1 or 2 after a second period of time,

3c: the schematic representation of a top view of a retaining element according to FIG

1 or 2 after a third period, and

4 shows the schematic representation of a cross section through a cartridge according to the invention comprising a retaining device according to FIG.

ADJUSTED SHEET (RULE 91) ISA/EP Embodiments of the invention

FIG. 1a shows a cross section of a first embodiment of a retaining device 4 according to the invention for separating cells located in a cell suspension. The retention device 4 comprises a feed unit 1, for example an inlet channel, and a retention element 2 with pores, for example a microfilter and/or a microsieve, and an outlet unit 3, for example an outlet channel. The retaining element 2 is at least partially made of an optically transparent material, such as a polycarbonate and/or a cycloolefin copolymer and/or a glass. The pores of the retaining element 2 have, for example, a diameter of 3 μm to 20 μm and preferably 4 μm to 8 μm. The retaining element 2 has, for example, an area of 1 mm ² -500 mm ² , and preferably 3 mm ² -100 mm ² , which can be exposed to a cell suspension. The retaining element 2 has, for example, a thickness of 0.9 μm-20 μm, and preferably 1 μm-12 μm. Furthermore, the restraining device 4 comprises an optical detection unit 5 which is arranged in such a way that it optically detects the surface of the restraining element 2 . The optical detection unit 5 is, for example, a CMOS (Complementary Metal Oxide Semiconductor) or CCD (Charge-Coupled Device)-based camera with a resolution of, for example, 1-4 MP depending on the area of the retaining element and with 1-10 fps depending on the flow rate.

The cells present in the cell suspension are marked, for example, in particular by means of fluorescent dyes, before they are fed to the retention device 4 . The cell suspension, in which the cells to be detected, which are marked for example, are present is fed to the retention device 4 via the feed unit 1 . The cell suspension is pumped through the retention device 4 at a constant flow rate or at a varying flow rate by means of a pump not shown in the figures. Here, the flow rate is in each case, for example, between 0.01 pl/s and 100 pl/s, and preferably between 0.2 pl/s and 5 pl/s. The cell suspension is fed to the retaining element 2, for example, all at once. Alternatively, the cell suspension is fed to the retaining element 2 in portions as aliquots and the cells retained by the retaining element 2 are after each aliquot or removed after a predetermined number of aliquots from the retaining element 2, e.g. by increasing the pressure difference across the retaining element or by lysing the retained cells. The cell suspension flows through the retaining element 2, which retains cells that are, for example, too large and too rigid to pass through the pores of the retaining element 2 and which cells that are, for example, small enough or deformable enough to pass through the pores of the retaining element 2, can pass through. While the cell suspension flows through the retention element 2, the cells retained by the retention element 2, for example marked cells and/or cells whose passage through the retention element 2 is delayed, are optically detected in real time by the optical detection unit 5. The real-time detection of the cells to be detected takes place, for example, by recording individual images at defined time intervals, in particular after 0.1-60 seconds, and preferably after 1-10 seconds, while the cell suspension is flowing through the retaining element 2 . In the case of fluorescence-marked cells to be detected, the real-time detection takes place, for example, by recording individual images at defined time intervals in each color channel required for the detection of the respective fluorescence marking. Depending on the marking, the detection thus takes place simultaneously in different color channels.

The recorded individual images are evaluated, for example, by evaluation software using an algorithmic method. The results of this analysis can be output in real time or alternatively after the cell suspension has passed through the retaining device 4 . The number of target cells can be determined at each recorded point in time.

In the case of marked cells, it can be concluded from the specific marking what kind of cell it is. Depending on the marking, this provides information about the number of living and dead cells, cells with and without a nucleus, and cells whose specific surface antigens are marked, so that it is possible to differentiate between target cells and non-target cells. In addition, information is obtained, for example, about how many detected target cells are present in the entire cell suspension and were retained or temporarily retained by the retaining element 2 .

In the case of real-time detection by the optical detection unit 5, other parameters can also be determined, such as the diameter, for example the detected cells and/or cell contour of the detected cells and/or transit time of the detected cells through the retaining element 2 and/or determination of the deformation of the detected cells when passing through the retaining element 2 and/or homogeneity of the agent embedded or bound in the detected cells Mark.

An example of the implementation of the method according to the invention is described below, with CTCs being separated from a blood sample by means of the retaining device 4 according to the invention.

First, the blood sample is mixed with 4-8 times the amount, preferably 5 times the amount, of a selective erythrocyte lysis buffer and incubated. As a result, the erythrocytes contained in the blood are lysed and the blood pigment hemoglobin is released into the solution.

The resulting suspension contains the intact cells, including the leukocytes and CTCs and the lysed erythrocytes, as well as free hemeglobin. The lysed erythrocytes and free hemoglobin are later separated by the retaining element 2 from the retained leukocytes and CTCs. After the erythrocyte lysis or at the same time as the erythrocyte lysis buffer is added, the cells contained in the cell suspension are marked, for example, without their viability being impaired and without them having to be fixed. For this purpose, for example, the fluorescent dye CFSE, which can only be detected in living cells, and/or the fluorescent dye PI is added to the cell suspension. Furthermore, for example, deoxyribonucleic acid-binding markers such as the fluorescent dyes DAPI and/or Hoechst3342, which mark cells containing a cell nucleus, are added to the suspension. In addition, for example, surface antigens such as EpCAM and/or cytokeratins, such as those found on CTCs, are labeled, for example by adding the fluorescence-labeled antibodies anti-EpCAM-allophycocyanin and/or the fluorescence-labeled antibodies anti-cytokeratin allophycocyanin. The suspension containing, for example, the fluorescence-marked cells is then fed to the retention device 4 via the feed unit 1 . The cell suspension flows through the retaining element 2, which retains cells that are too large and stiff to pass through the pores of the retaining element 2 and which allows cells that are small enough or deformable enough to pass through the pores of the retaining element 2 to pass through . During the flow of the cell suspension through the retaining element 2, the marked cells retained by the retaining element 2 and/or marked cells whose passage through the retaining element 2 is delayed are optically detected in real time by the optical detection unit 5 . The real-time detection takes place, for example, by recording individual images at defined time intervals in each color channel required for the detection of the respective fluorescent marking.

Based on the specific marking of the detected cells in the cell suspension, information is obtained about the number of living and dead cells, nucleated and nucleated cells and cells whose specific surface antigens are marked. With this information, a distinction can be made between a CTC and a leukocyte. In addition, information is obtained, for example, about how many detected CTCs were present in the entire cell suspension and were retained or temporarily retained by the retention element 2 . The number of CTCs can be determined at each recorded point in time. Further parameters of the CTCs can also be determined, such as the localization of the detected CTCs on the restraint element 2 and/or the diameter of the detected CTCs and/or the cell contour of the detected CTCs and/or the transit time of the detected CTCs through the restraint element 2 and /or determination of the deformation of the detected CTCs when passing through the retaining element 2 and/or the homogeneity of the means for marking embedded or bound in the detected CTCs. All of the variants described above for FIG. 1 are compatible with the exemplary embodiment described for separating CTCs from a blood sample.

In FIG. 1b, the restraining device 4 according to FIG. 1a is shown in a plan view. The feed unit 1, the retaining element 2 with pores, and the discharge unit 3 can be seen. The optical detection unit 5 is not shown.

FIG. 2 shows a top view of a restraining device 4 according to the invention in a second embodiment. The restraining device 4 has a feed unit 1 with a first feed channel la and with a second feed channel lb. When the cell suspension flows through the retention element 2, a more homogeneous distribution of the cell suspension on the retention element 2 is achieved in comparison to a retention device 4 with only one feed channel. The feed channels la, lb connect to form a large feed channel via the retaining element. Alternate and not in the figure shown, the supply channels la, lb do not connect via the retaining element.

Furthermore, the retention device 4 has a drainage unit 3 with a first drainage channel 3a and a second drainage channel 3b, through which the cell suspension drains after it has passed the retention element 2 . Alternatively and not shown, the drain unit 3 includes only one drain channel. This has, for example, a larger diameter than the feed channels 1a and 1b of the feed unit 1. In a further embodiment, not shown, the retaining device 4 comprises a plurality of feed ducts and one or more outlet ducts.

All the variants described above for FIGS. 1a and 1b are compatible with the second embodiment of the restraining device 4 described.

In each of FIGS. 3a-3c, a retaining element 2 according to one of FIGS. 1 or 2 is shown in a plan view. A cell suspension flows through the retaining element 2 . In FIG. 3a the retaining element 2 is shown after a first period of time, in FIG. 3b the retaining element 2 is shown after a second period of time and in FIG. 3c the retaining element 2 is shown after a third period of time.

In Figure 3a, after a first period of time, a first cell 6a and a second cell 6b are retained by the retaining element 2, since the cells have, for example, a larger diameter than the pores of the retaining element 2. In Figure 3b, after a second period of time, the first Cell 6a and the second cell 6b and a third cell 6c are retained by the retaining element 2. The third cell 6c also has, for example, a larger diameter than the pores of the retaining element 2. In FIG. 3c, the first cell 6a and the third cell 6c are still retained by the retaining element 2 after a third period of time. The second cell 6b is no longer located on the restraining element 2. It has passed the restraining element 2 with a delay, for example due to a cell deformation.

The periods of time shown correspond, for example, to the times at which individual images are recorded during real-time detection while the cell suspension is flowing through the retaining element 2 . Here, both of the retaining element 2 are permanently retained Cells, here the cells 6a and 6c are detected, as well as cells which pass the retaining element 2 with a time delay, here the cell 6b.

The cells 6a, 6b and 6c have different diameters and cell contours. Among other things, these parameters can also be detected, for example, by the optical detection unit 5 in real-time detection.

FIG. 4 shows a cross section through a cartridge 10 according to the invention, in particular a microfluidic cartridge, which has a retaining device 4 according to FIG. The retention device 4 is designed as a microfluidic system and includes a feed unit 1, for example an inflow channel, a retention element 2 with pores, for example a microfilter and/or a microsieve, and an outflow unit 3, for example an outflow channel. Alternatively and not shown in FIG. 4, the cartridge 10 comprises a retaining device 4 in the second embodiment as shown in FIG. The steps for separating cells in a cell suspension described in FIGS , as well as process steps for marking the cells to be detected in the cell suspension. In addition, the cells retained by the retaining element 2 can be lysed in real time after detection within the cartridge 10 and the cell lysate can then be transported, for example, into an additional sample chamber on the cartridge 10 . In this, the DNA and/or RNA of the lysed cells are extracted, for example for further analysis, without the need for an additional external system.

Claims

Expectations

1. Retaining device (4) for separating cells in a cell suspension, comprising at least one feed unit (1) and a retaining element (2), in particular a microfilter and/or a microsieve, with pores, characterized in that the retaining device (4 ) further comprises an optical detection unit (5) for optical real-time detection of cells retained by the retaining element (2) and/or cells whose passage through the retaining element (2) is delayed.

2. Device according to claim 1, characterized in that the retaining element (2) is made at least partially from an optically transparent material, in particular from a polycarbonate and/or a cycloolefin copolymer and/or a glass.

3. Device according to one of the preceding claims, characterized in that the pores of the retaining element (2) have a diameter of 3 pm -20 pm, preferably 4 pm - 8 pm.

4. Device according to one of the preceding claims, characterized in that the retaining element (2) has an area of 1 mm ² - 500 mm ² , preferably 3 mm ² - 100 mm ² , which can be exposed to a cell suspension.

5. Device according to one of the preceding claims, characterized in that the retaining element (2) has a thickness of 0.9 pm - 20 pm, preferably 1 pm - 12 pm.

6. A method for separating cells in a cell suspension, in particular living cells, by means of a retaining device (4) according to one of claims 1-5 with the following steps: b) Supplying the cell suspension to the device (4) with the retaining element (2) c) Optical detection of the cells retained by the retaining element (2) and/or the cells whose passage through the retaining element (2) is delayed, the detection in Takes place in real time while the cell suspension is flowing through the retaining element (2).

7. The method of claim 6, wherein step b) is preceded by an additional step a): a) labeling of the cells to be detected in the cell suspension, wherein in particular the viability of the cells to be detected is retained, and wherein in step c) the optical detection of through the restraining element

(2) retained, marked cells and/or marked cells whose passage through the retaining element (2) is delayed, and the detection takes place in real time while the cell suspension is flowing through the retaining element (2).

8. The method according to claim 7, wherein the cells to be detected are marked by staining with carboxyfluorescein succinimidyl ester and/or with propidium iodide and/or by labeling of surface antigens, in particular by fluorescent antibodies and/or by means of a label that binds deoxyribonucleic acid.

9. The method according to any one of claims 6-8, wherein in step c) at least one of the following parameters is detected: number of cells to be detected and / or diameter of the cells to be detected and / or cell contour of the cells to be detected and / or transit time of the cells to be detected by the retaining element (2) and/or determination of the deformation of the cells to be detected when passing through the retaining element (2) and/or homogeneity of the labeling agent embedded or bound in the cells to be detected

10. The method as claimed in any of claims 6-9, characterized in that the cells to be detected are detected by recording individual images at defined time intervals, in particular after 0.1-60 seconds, preferably after 1-10 seconds.

11. The method according to any one of claims 6-10, wherein the cell suspension is a blood sample, in particular a pretreated blood sample.

12. The method according to any one of claims 6-11, wherein the cells to be detected are circulating tumor cells.

13. The method according to any one of claims 6-12, wherein a pump pumps the cell suspension at a constant flow rate or at a varying flow rate through the retention device (4), and wherein the flow rate is in particular between 0.01 pl/s and 100 pl/s , preferably between 0.2 pl/s and 5 pl/s.

14. The method according to any one of claims 6-13, wherein the cell suspension is fed to the retaining element (2) in portions as aliquots and the cells retained by the retaining element (2) are removed from the retaining element (2) after each aliquot or after a predetermined number of aliquots will.

15. cartridge (10), in particular microfluidic cartridge, comprising a retaining device (4) according to any one of claims 1-5.